Ablation system, clamp and method of use

ABSTRACT

A method and apparatus for ablating tissue are disclosed that comprise positioning two or more bi-directional ablation energy sources in spaced-apart relation in sufficient proximity to the tissue to be ablated so that, upon activation each energy source creates an energy field in the tissue to be ablated. The energy sources are spaced such that the energy fields created by at least one of the activated sources partially overlaps with the energy field created by one or more of the other energy sources. The energy sources are alternately activated and deactivated, so that a substantially constant energy field results where the energy fields created by at least two of the energy sources overlap. While the energy sources are preferably RF energy sources, other energy sources, such as microwave, may be used.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No. 17/033,713 filed Sep. 26, 2020, which is a continuation of U.S. patent application Ser. No. 15/897,514 filed Feb. 15, 2018, now U.S. Pat. No. 10,792,091, which is a continuation of U.S. patent Ser. No. 11/970,005 filed Jan. 7, 2008, now U.S. Pat. No. 9,924,998 which claims the benefit of U.S. Provisional Application No. 60/884,783, filed Jan. 12, 2007, and also claims the benefit of U.S. Provisional Application No. 60/884,719, filed Jan. 12, 2007, each of which is incorporated by reference in their entirety.

FIELD OF THE INVENTION

The present invention relates, in general, to methods and apparatus for tissue ablation instruments and, more particularly, to devices, systems, and methods using resistive and thermal heating for the ablation of tissue.

BACKGROUND OF THE INVENTION

It is known to use bipolar RF energy devices that clamp tissue between opposed electrodes and apply RF energy to heat tissue to form lines of ablation on the tissue. This has found particular application in the formation of strategically located lines of ablation in cardiac tissue to block spurious electrical signals to the heart, which has been particularly beneficial in the treatment of atrial fibrillation. See, e.g., U.S. Pat. No. 6,889,694, which is incorporated herein by reference.

Such bipolar electrode devices apply energy directly to the surface of tissue clamped between a first electrode and a second electrode. The first electrode, the clamped tissue, and the second electrode, form a conductive resistive circuit. As the moisture in the tissue conducts the RF energy, the tissue begins to desiccate. As the tissue desiccates, it becomes more resistive. The application of bipolar RF energy on tissue shows that tissue desiccation progresses inwardly from the outside or surface of the tissue near the electrode-tissue contact area, where the current flux or density is greatest. Surface desiccation increases resistance in the tissue and can make it more difficult to achieve good depth of penetration in underlying tissue without creating a larger than desired area of ablated tissue or excessive surface heating adjacent to the electrodes. A recent study reported that to achieve a depth of ablation of 5 mm, a width of ablation of almost 8 mm wide in the endocardium resulted. See “Mechanism, Localization, and Cure of Atrial Arrhythmias Occurring After a New Intraoperative Endocardial Radiofrequency Ablation Procedure for Atrial Fibrillation,” Thomas et al., Journal of the American College of Cardiology, Vol. 35, No. 2, 2000, hereby incorporated by reference. While a wider ablation facilitates the surgeon's visual confirmation that an ablation has been created, it is still desirable to control the width of ablation so as to keep the width of the ablation and thermal spread from the zone of ablation within certain limits so as to not irreversibly damage more cardiac tissue than necessary.

To overcome surface tissue heating effects, techniques such as cooling or cryogenics have been used, and selected positioning of the electrodes has been considered. See, for example, U.S. Pat. No. 6,413,253 to Koop et al., U.S. Pat. No. 6,629,535 to Ingle et al., and U.S. Pat. No. 7,022,121 to Stern et al. and U.S. Pat. No. 6,918,906 to Long.

Consequently, a significant need exists for an improved electrosurgical device and method of use that can enhance lesion formation and provide for more efficient ablation.

SUMMARY OF THE INVENTION

The invention provides for an apparatus and system for ablating tissue, along with a method of use that comprises an energy generator and a plurality of ablation energy sources that are adapted to be positioned in proximity to the tissue to be ablated. Each energy source is in operative communication with the generator, and each source, when activated, generates an energy field that at least partially overlaps with an energy field created by one or more of the other sources. A control system is provided that is operatively associated with both the generator and the sources to alternately activate and deactivate the sources so that a substantially constant energy field is created in the area of overlap.

More specifically, and without limiting the foregoing, a method of tissue ablation using RF electrodes is provided in which the tissue to be ablated is contacted with a plurality of electrode pairs, the electrodes of each pair being of opposite RF energy polarity so as to provide a current flux between the members of each pair when activated. The electrode pairs are then alternately activated and deactivated with RF energy to create at least one zone of primary heating in the tissue that is spaced from or substantially non-coincident with at least one zone of the highest current flux in the tissue. This is unlike the prior art devices where the zones of primary heating and highest current density substantially coincide or are contained in the same space and are located at the electrode-tissue interface.

In another aspect of the invention, a tissue ablation method is provided that comprises positioning two or more preferably bi-directional ablation energy sources in spaced-apart relation in sufficient proximity to the tissue to be ablated so that, upon activation, each energy source creates an energy field in the tissue to be ablated. The energy sources are spaced such that the energy fields created by at least one of the activated sources partially overlaps with the energy field created by one or more of the other energy sources. The energy sources are alternately activated and deactivated so that a substantially constant energy field results where the energy fields created by at least two of the energy sources overlap. While the energy sources are preferably RF energy sources, other energy sources, such as microwave, ultrasound (especially High-Intensity Focused Ultrasound or HIFU), laser, etc., may be used.

More specifically, a tissue ablation apparatus is provided that comprises opposed relatively moveable jaws for clamping the tissue to be ablated therebetween. A plurality of electrode pairs is provided one electrode of each pair being carried on one jaw and being adapted to be connected to one terminal of an RF generator, and the other electrode of each pair being carried on the other jaw and being adapted to be connected to the opposite terminal of an RF generator. A current flux is created between the respective electrodes of each pair when activated by the generator. The electrode pairs are located on the jaws such that when alternately activated and deactivated by an RF generator, the electrodes create at least one flux zone of primary heating in the tissue that is spaced from at least one flux zone of the highest current flux in the tissue.

In another aspect of the invention, the method can be practiced, and the device can be provided with multiple pairs of energy sources or electrodes. For example, if two pairs are provided, one zone of overlap results. If three pairs are provided, two zones of overlap result. If four pairs are provided, three zones of overlap result, etc. The number of pairs of energy sources can be selected to provide an ablation line, area, or zone of the desired width.

In another aspect of the invention, sufficient pressure is applied to the tissue to be ablated to reduce its moisture content, and also to normalize the impedance within the tissue, and provide good contact between the electrodes and the tissue to normalize the electrode to tissue impedance. Preferably, the pressure applied to the tissue is proportional to its thickness, i.e., increasing pressure with increasing tissue thickness. This pressure may be the result of clamping force, suction, or other means.

In another aspect, the method and device may utilize impedance and/or temperature sensors to control the energy delivered to the instrument.

These and other aspects and advantages of the present invention will become apparent from the accompanying drawings and the following detailed description.

BRIEF DESCRIPTION OF THE FIGURES

The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate embodiments of the invention and, together with the general description of the invention given above and the detailed description of the embodiments given below, serve to explain the principles of the present invention.

FIG. 1 is a perspective view of a system according to the present invention, including an RF energy generator and a cardiac ablation clamp having opposed jaws.

FIG. 2 is an enlarged fragmentary perspective view of the opposed jaws of the ablation clamp shown in FIG. 1 .

FIG. 3 is a plan view of one of the jaws of the ablation clamp of FIG. 1 .

FIG. 4 is an enlarged cross-sectional view of the opposed jaws of the RF ablation clamp of FIG. 1 taken along line 4-4 of FIG. 3 .

FIGS. 5-7 illustrate the creation of overlapping energy fields between two pairs of spaced apart electrodes by alternately energizing the electrodes of each pair in accordance with the method of the present invention.

FIGS. 8-10 sequentially illustrate the formation of a lesion in tissue held between opposed jaw members having two pairs of opposed electrodes in accordance with practicing the method of the present invention.

FIGS. 11-13 illustrate the creation of overlapping energy fields when three pairs of opposed electrodes are used in accordance with the method of the present invention.

FIG. 14 is a cross-sectional view of tissue comparing the profile of the ablated tissue when the method according to the present invention is performed and that obtained by practicing the prior art.

DETAILED DESCRIPTION

The following description of certain examples of the invention is not intended and should not be used to limit the scope of the present invention. Other examples, features, aspects, embodiments, and advantages of the invention will become apparent to those skilled in the art from the following description, which is by way of illustration of one or more of the best modes contemplated for carrying out the invention. As will be realized, the invention is capable of other different and obvious aspects, all without departing from the invention. Accordingly, the drawings and descriptions should be regarded as illustrative in nature and not restrictive.

As described above, radio frequency (RF) energy can be used in electrosurgical systems for heating, coagulation, or ablating tissue. Monopolar and bipolar RF systems are known to those skilled in the art, and it is well known to use a bipolar electrosurgical clamping device. Bipolar electrosurgical instruments apply energy between a pair of electrodes in direct contact with the tissue to be ablated and provide more precise control of the extent of ablation than monopolar energy. It is well known to use a bipolar electrosurgical clamping device with a pair of opposed RF electrodes to clamp and ablate tissue therebetween, and the ablated tissue may produce a generally continuous lesion which can be well suited for the treatment of cardiac arrhythmias. The Atricure Isolator® and ASU from Atricure, Inc. of Cincinnati, Ohio, is a system useful for such treatment of atrial fibrillation,

In accordance with one aspect of the present invention, FIG. 1 illustrates an example of a tissue ablation system in the form of a bipolar electrosurgical system 10 having an electrosurgical instrument 12 coupled to an energy generator, e.g., an RF generator 14. Electrosurgical instrument 10 preferably comprises a handle 16, an elongated longitudinal shaft 17 extending therefrom, and an end effector 18 for clamping and heating tissue therebetween. Although illustrated as a damping device particularly suited for open procedures where the ablation site is directly viewable by the surgeon, the present invention is also well suited for minimally invasive procedures, such as intercostal or subxyphoid approaches to cardiac tissue targeted for ablation.

The illustrated end effector 18 has first and second opposed jaws for damping tissue therebetween, henceforth referred to for convenience as proximal jaw 20 and distal jaw 22. The proximal and distal jaws 20 and 22 are shown spaced apart for the reception of tissue therebetween, but at least one of the proximal and distal jaws 20 22, respectively, could be movable to clamp tissue therebetween. To this end, proximal and distal jaws 20, 22 may be operably coupled to a closure trigger 24 extending proximally from the handle 16 such that it is operable with one hand so that distal movement of the closure trigger 24 brings the proximal and distal jaws 20, 22 together. Likewise, proximal movement of closure trigger 24 moves the proximal and distal jaws 50 55 apart. The proximal and distal jaws 20, 22 are shown extending at an angle from the shaft 16 but can be at any angle with the shaft 17. The present invention is not limited to the particular mechanism for moving the jaw(s), and an example of such a mechanism may be found in U.S. Pat. No. 6,923,806 and U.S. application Ser. No. 10/263,386, filed Oct. 2, 2002, both of which are incorporated by reference herein.

The invention provides for a method, apparatus, and system for ablating tissue that comprises positioning two or more preferably bi-directional ablation energy sources in spaced-apart relation in sufficient proximity to the tissue to be ablated so that, upon activation each energy source creates an energy field in the tissue to be ablated. The energy sources are spaced such that the energy fields created by at least one of the activated sources partially overlap with the energy field created by one or more of the other energy sources. The energy sources are alternately activated and deactivated so that a substantially constant energy field results where the energy fields created by at least two of the energy sources overlap. While the energy sources are preferably RF energy sources, other energy sources, such as microwave, may be used.

To that end, and in keeping with one aspect of the invention that employs RE energy, two or more pairs of opposed electrodes are located in proximal and distal jaws 20, 22 of the instrument 12. All of the electrodes are operably coupled to the RF generator 14 by a cable 26 and can be operator actuated by a switch, such as a foot switch extending therefrom, A control system/RF generator for providing RF energy and for use in the system of the present invention is shown in the co-pending application U.S. Ser. No. 60/884,783, filed Jan. 12, 2006 in the name of Chris Park et al. entitled Matrix Router with Frequency Switching, and in U.S. Ser. No. 11/457,531, filed Jul. 14, 2006, which claims the benefit of U.S. Ser. No. 60/699,664, filed Jul. 15, 2005, all of which are incorporated herein by reference.

The RF energy monitored impedance delivered to the electrode pairs is preferably based, at least in part, on the monitored impedance of the tissue to be ablated as it is held between the jaws of the instrument. To this end, the controller preferably monitors or senses voltage and/or currents associated therewith, calculating or deriving the impedance of the tissue between the electrodes of at least one of the pairs of opposed electrodes and preferably between at least two of the pairs of opposed electrodes. The ablation may continue until the calculated Impedance indicates that the lesion or ablation line is transmural (or fully through the tissue thickness).

With reference to FIGS. 2-4 , an electrosurgical instrument 12 according to the present invention having two pairs of opposed electrodes is shown. The proximal jaw 20 has a first electrode 28 and a second electrode 30 in a proximal insulator 32 that extends along the length and across the width of the jaw. The electrodes 28, 30 are preferably centered laterally on the insulator 32 about the medial plane of the jaw and spaced apart a distance 34 from about 0.7 mm to 4 mm, the distance being a factor of the thickness of the tissue to be ablated. Other factors influencing the distance 34 between the electrodes include the type of tissue (e.g., cardiac, skeletal muscle, or smooth muscle, such as the small bowel or uterus wall), the frequency of energy source switching, the desired duration of ablation, and the desired width of ablation. If the tissue to be ablated is about 5 mm thick (uncompressed), which is typical of cardiac tissue, the preferred electrode spacing is approximately 1.0 mm. As the spacing of the electrodes is increased, it is preferred that the insulator surface be convex so that the desired increased pressure on the tissue between the electrodes is achieved. With two pairs of opposed electrodes, the crown radius of the insulator of a preferred embodiment is about 4.5 mm, and its face width is about 5 mm. These dimensions are illustrative only, and other dimensions may be used without departing from the present invention in its broader respects.

The distal jaw 22 is configured similarly to the proximal jaw 20 and has a third electrode 36, preferably directly opposite to the first electrode 28, and a fourth electrode 38, preferably directly opposite to the second electrode 30. Electrodes 36, 38 are mounted in a distal insulator 40 with an electrode spacing 42, preferably matching the spacing in the proximal jaw so that the electrodes in each pair are in opposed relation. Electrodes 28, 30, 36, 38 are preferably identical in size and shape and preferably have a beryllium-copper base with a nickel/gold plating covering all exposed surfaces. The electrodes have a preferred electrode width 44 of about 0.012 inches and extend from the surface of the insulator over the length of the ablation surface from about 0.000 mm to about 0.15 mm. Other widths and projections may also be used.

With reference to FIGS. 5-7 , the four electrodes 28, 30, 36, 38 can form parallel dual electrode arrays that can be pulsed. That is, electrodes 28 and 36 define one ablation energy source in the form of one pair of opposed electrodes having opposite polarity, and electrodes 30 and 38 define another energy source in the form of a second pair of opposed electrodes that have opposite polarity. Although in the drawings, the electrodes on each jaw are indicated as being of the same polarity, the electrodes on each jaw may be of the same or opposite polarity without departing from the invention. When energized by the RF generator, electrical current flows between the electrodes, creating an energy field in the form of current flow or flux between the electrodes that generally, for purposes of illustration, is shown in FIGS. 5 and 6 . As can be seen there, the current density is highest at the electrode surfaces, i.e., at the interface between the electrodes and the tissue, which, prior to the present invention, would also be expected to be the area of primary tissue heating. However, in accordance with one aspect of the present invention, the two energy sources or pairs of opposing electrodes can be pulsed by energizing the first electrode pair 28, 36 for a timed duration (FIG. 5 ), turning the first electrode pair 28, 36 off and energizing the second electrode pair 30, 38 for the another, preferably the same, timed duration (FIG. 6 ), turning the second electrode pair 30, 38 off and repeating the pulsing cycle (alternately energizing and de-energizing the first electrode pair 28, 36 and the second pair 30, 38), thus creating an area of overlapping current flux 44 (FIG. 7 ). The overlapping area of current flux is thus subjected to a substantially continuous current flow, while the other tissue, including tissue at the electrode interface, experiences only intermittent current flow. As a result, a zone of primary tissue heating is created in the area of overlap, which is spaced from the area of highest current density.

The cycling of the electrodes is preferably repeated until the ablation of the tissue is transmural. Thus, to achieve a transmural ablation line, the opposing pairs of electrodes are cycled in a series of on-off first pair and on-off second pair cycles until ablation is complete. It has been determined that transmural ablation is achieved when the temperature of the tissue reaches approximately 50° C. Thus, one or more temperature sensors may be associated with the jaws to provide an indication of the progress of ablation. The temperature sensor(s) may be located on one or both jaws between the electrodes forming part of each opposed pair or on the jaws outside of the electrodes to detect thermal spread, which is the lateral spread of heat from the area or zone of ablation into tissues outside the zone.

FIGS. 8-10 illustrate the proximal and distal jaws 20, 22 clamped on tissue 48 of a tissue thickness 50. The clamping pressure is pressing the jaws 20, 22 into the tissue to create a jaw gap 52 that is typically less than the tissue thickness 50. The clamping pressure may be controlled by a tissue pressure system, such as a lost motion means, located in the handle of the electrosurgical device in a manner known as the prior art. Note that the tissue is compressed between two arcuate surfaces formed from the electrodes 28, 30, 26, 38 and the proximal insulator 32 and the distal insulator 40. These arcuate surfaces preferably apply the highest tissue pressure across the narrowest clamp gap 52, and the electrodes 28, 30, 36, 36, 38 flank this high pressure region. The pressure exerted on the tissue to be ablated is preferably sufficient to reduce the moisture in the tissue held between the jaws. This pressure is proportional to the thickness of the tissue to be ablated and is typically between about 10 and 23 psi for typical cardiac tissue having an uncompressed thickness of about 5 mm, with a preferred clamping pressure of about 16 psi. for cardiac tissue having a compressed thickness of about 2 mm.

As indicated above, by energizing the electrodes alternately, as shown in FIGS. 5-7 , a zone of primary heating is created in tissue held therebetween where there is a continuous flux, that is, where the fluxes overlap, as designated 44 in FIG. 7 . A zone of primary heating results that is offset from the zones of highest current density, which is directly between the electrodes of each pair, as shown in FIGS. 5 and 6 . The pulsing frequency is preferably between about 2 and 575 Hz, and more preferably between about 10 and 376 Hz, with a higher frequency being preferred for ablating thinner tissue structures and a lower frequency being preferred for thicker tissue structures. The alternate energizing or pulsing of the electrodes means that the electrodes energized only 50 percent of the time if the on-off cycles are identical. This half-duty cycle provides for balanced ablation and allows the electrode surfaces to be substantially cooler than if they were operated continuously. As a result, ablation 54 starts centrally in the tissue in the zone of primary heating and gradually extends or expands outwardly toward the jaw surfaces, as shown in FIGS. 8-10 , Because the ablation does not start at the electrode surface, the impedance at the electrode surface does not increase as rapidly as with a single pair of opposed electrodes, resulting in a more efficient ablation process. If desired, the duty-cycle could be something other than half-on, half-off, such as 60% on, 40% off, to achieve an ablation biased to one side or the other.

With reference to FIGS. 11-13 , the present invention also contemplates using multiple energy sources, for example, three or more pairs of opposed electrodes and alternately energizing the adjacent electrodes. With reference to FIGS. 11-13 , for example, three pairs of opposed electrodes are schematically illustrated, with the outer two pairs being fired simultaneously (FIG. 11 ) and then being deactivated with the central electrode pair being fired (FIG. 12 ) to result in two zones of primary heating being created between the jaws corresponding to the two zones of overlapping current flux, both zones being spaced from the zones of highest current density that occurs directly between the electrodes of each pair and at the electrode-tissue interface. The number of electrode pairs utilized is selected based upon the desired width of the ablation line to be obtained. The number of electrode pairs may be more than three pairs and may be an even or odd number of electrode pairs.

With reference to FIG. 14 , there is a representation in the cross-section of tissue 60 ablated with a device having a single pair of opposed electrodes and with a device having two pairs of opposed electrodes operated according to the methods described above. The ablation line cross-section 62, resulting from the use of two pairs of electrodes, is wider than the ablation line cross-section 64, resulting from a similarly configured instrument having a single pair of opposed electrodes, resulting in an ablation line that is more visible to the surgeon. However, the ablation line 62 continues to be maintained within the width of the jaws and forms a relatively well-defined line of ablation with limited lateral extent and limited thermal spread to adjacent tissue. Thus, the device of the present invention provides for wider ablation lines that are well-defined and do not spread beyond the width of the jaws. Ablations obtained by use of the present invention are also wider at the core than those using a single pair of opposed electrodes and have more of a barrel shape than an hourglass shape as shown in the drawing.

It should be appreciated that any patent, publication, or other disclosure material, in whole or in part, that is said to be incorporated by reference herein is incorporated herein only to the extent that the incorporated material does not conflict with existing definitions, statements, or other disclosure material set forth in this disclosure. As such, and to the extent necessary, the disclosure as explicitly set forth herein supersedes any conflicting material incorporated herein by reference, Any material, or portion thereof, that is said to be incorporated by reference herein but which conflicts with existing definitions, statements, or other disclosure material set forth herein will only be incorporated to the extent that no conflict arises between that incorporated material and the existing disclosure material.

While the present invention has been illustrated by description of several embodiments and while the illustrative embodiments have been described in considerable detail, it is not the intention of the applicant to restrict or in any way limit the scope of the appended claims to such detail. For example, while the invention has been described as using bipolar RF energy, other energy sources may be used, such as microwave energy. Additional advantages and modifications may readily appear to those skilled in the art. 

1. A method, comprising: clamping cardiac tissue between opposing jaws of an ablation clamp to apply pressure to the cardiac tissue proportional to a thickness of the cardiac tissue, wherein the jaws each comprise an electrode; and energizing the electrodes with electric current by pulsing the electric current to form a transmural lesion in the cardiac tissue.
 2. The method of claim 1, further comprising clamping the jaws to create a jaw gap that is less than a thickness of the cardiac tissue.
 3. The method of claim 1, wherein one or more of the jaws comprise an insulator comprising a convex surface and one or more of the electrodes is centered laterally on the insulator.
 4. The method of claim 1, wherein the applied pressure is between about 10 pounds per square inch (PSI) and about 23 PSI.
 5. The method of claim 1, wherein the jaws each comprise an arcuate surface formed from one of the electrodes and an insulator and the method further comprises compressing the cardiac tissue between the arcuate surfaces to apply the pressure to the cardiac tissue.
 6. The method of claim 5, further comprising applying a highest pressure to the tissue at a narrowest gap between the arcuate surfaces.
 7. The method of claim 1, wherein respective energy fields of the electrodes resulting from the pulsing of the electric current at least partially overlap.
 8. The method of claim 7, further comprising electrically energizing the electrodes, wherein the energy fields comprise current fluxes of the electrodes.
 9. The method of claim 1, wherein the transmural lesion is formed proximate energy fields of the electrodes resulting from the pulsing of the electric current.
 10. The method of claim 1, wherein one or more of the electrodes are energized by an energy source comprising a radiofrequency, microwave, ultrasound, or laser energy source.
 11. The method of claim 10, wherein the ultrasound energy source comprises a high intensity focused ultrasound (HIFU) energy source.
 12. The method of claim 1, wherein the electrodes comprise a pair of opposed electrodes having opposite polarity.
 13. The method of claim 1, further comprises repeating the pulsing over multiple pulsing cycles.
 14. The method of claim 1, wherein one or more of the jaws comprises an insulator comprising a convex surface and one or more of the electrodes is centered laterally on the insulator. 